【発明の詳細な説明】この発明は血圧゛？連続的かつ全自動的に測定でさるよ
うにした間接的血圧測定方法に関する。[Detailed Description of the Invention] This invention is based on blood pressure? This invention relates to an indirect blood pressure measurement method that performs continuous and fully automatic measurement.
周知θつように従来一般の血圧測定装置１′１は、適当
な劾ｊ↓ｊ１テ、例えば腕の動脈に外部から圧力を加え
るとその圧力が最高血圧以上ならばこび）動脈に血流が
なくケリ、散設！・血圧と最低面圧との中間にあれはこ
の切１！ｉ Ｖｃ圧着した血流−ざ検出器に血流音が検
出され、ｉたＩＤＰｉ、圧力が最低血圧より低くなれば
面幅は存在しても血流音は生じないか′ｆには極めてＯ
？１．弱となること？利用して、最高血圧、最低血圧の
何れ力）一方ど連続的に測定する装置ぞある。As is well known, the conventional general blood pressure measuring device 1'1 calculates the blood flow in the artery by applying an external pressure to the artery in the arm (if the pressure exceeds the systolic blood pressure). Nakubuteri, scattered!・That is the cutout between the blood pressure and the lowest surface pressure! If the blood flow sound is detected by the blood flow detector that is crimped to Vc, and the pressure is lower than the diastolic blood pressure, there will be no blood flow sound even if the surface width is present.
? 1. To be weak? There are devices that can be used to continuously measure both systolic and diastolic blood pressure.
Ｌ力・し上記のような血圧測定装置においては、最高血
圧、最低血圧のうち何れか一方しか連続的に測定と行う
ことがでさす、最高、最低血圧を共に同時に測定？行い
たい場合の要求？満足することかでさなかった。疋た最
高、最低血圧の同時測定のみならず血圧波形の全変動状
態を記録することは、医学上さねめで利用範囲が広く、
従来このような血圧測定装置ａは要望ざｎながらも・こ
ｑ要望に応える装置がみあたらなかった。With the blood pressure measuring device described above, only one of the systolic and diastolic blood pressures can be measured continuously.Can both the systolic and diastolic blood pressure be measured at the same time? Request if you want to do it? I was not satisfied. Not only the simultaneous measurement of maximum and diastolic blood pressure, but also the recording of all fluctuations in the blood pressure waveform is medically important and has a wide range of applications.
Conventionally, there has been a demand for such a blood pressure measuring device (a), but no device has been found that meets this demand.
そこで、本出願人は先に特願昭５２−ＩＬｆｉΦ（）２
号において、容積補償法によって最高血圧、最低血圧お
よび血圧波形の全変動状態ビ測定する装置ｎと提案した
この容積補償法による血圧測定は生体外から血管に外圧
を加え脈動する血管の逆位長当りの容積を一定に保つこ
とで生体外圧と血管内圧すなわち血圧と？平衡させ、こ
の状態と維持して前ｎｅｌｆ’ｐ圧？測定することによ
り血圧の連続測定２行うものである。Therefore, the present applicant first applied for the patent application No. 52-ILfiΦ()2.
In this issue, we proposed a device for measuring systolic blood pressure, diastolic blood pressure, and all fluctuations in blood pressure waveforms using the volume compensation method. Blood pressure measurement using this volume compensation method involves applying external pressure to a blood vessel from outside the body and measuring the inverted length of a pulsating blood vessel. By keeping the per unit volume constant, the external pressure and intravascular pressure, that is, blood pressure? Equilibrate and maintain this state before nelf'p pressure? By measuring blood pressure, continuous measurement 2 is performed.
ところで、上述した先願装置においては後述するサーボ
目標Ｉｌαの設定や血圧測定の記録などｂで特殊な測定
技術が要求されるとともｔ／ｃ測定操作が相当ｖｃ繁雑
であった。By the way, in the device of the prior application described above, special measurement techniques are required for setting the servo target Ilα, recording of blood pressure measurement, etc., which will be described later, and the t/c measurement operation is considerably complicated.
こα）発明は上記の串消に話み、血圧と連続的かつ全自
動的に測定する間捉的血圧ン則定方法？提供するもので
、カフを介して被測定部位の動脈に外圧（カラ圧）？加
え、この動脈の血圧とカフ圧とと一致させる過程と、前
記血圧とカフ圧とが一致したとざのカフ圧？血圧として
表示する過程と？全自動的に行うことを特徴とする。This α) invention is based on the above-mentioned question, and is an intermittent blood pressure determination method that continuously and fully automatically measures blood pressure? Does it provide external pressure (cara pressure) to the artery at the measurement site through the cuff? In addition, the process of matching the arterial blood pressure with the cuff pressure, and the cuff pressure at the point where the blood pressure and cuff pressure match? What is the process of displaying it as blood pressure? It is characterized by being fully automatic.
以下、この発明について詳細Ｑで説明する。This invention will be explained in detail below.
乏ず、この発明による血圧測定方法の原理について説明
する。この発明は容積補償法に基づくものである。容積
補償法は血管に流れる血液の圧力（血圧）Ｐ６と血管に
かかる外圧（カフ圧）Ｐｃとを常時一定に保つことによ
り、血管壁と無負荷状−（すなわち圧力のか力）らｌい
自然な状し）に維付し、こりとさのカフ圧を血圧として
抽出する方法である。従って容積補償法で血圧の測定と
行うには、Ｈｊｉ ｆが無負荷状態にあること？検出す
ることと・この状態と維持することの１点が最も重要な
課題となる。First, the principle of the blood pressure measuring method according to the present invention will be explained. This invention is based on a volume compensation method. The volume compensation method maintains the pressure of blood flowing through the blood vessel (blood pressure) P6 and the external pressure (cuff pressure) Pc applied to the blood vessel at a constant constant level, thereby naturally reducing the unloaded state (i.e., pressure force) between the blood vessel wall and the blood vessel wall. In this method, the cuff pressure of the stiffness is maintained as the blood pressure. Therefore, in order to measure blood pressure using the volume compensation method, Hjif must be in an unloaded state. The most important issues are detection and maintenance of this state.
ところで、脈圧Ｏでよる血管壁の振動の振幅は、平均カ
フｌ（： Ｊ’ ｃと平均血圧Ｆ１とが一致したとさに
最大となることが知られている。そして、血管壁ｃｖ伽
’ｉ’ｆＪは血管の単位長当りの容積（以下単に血戦二
の容積という）とｌ対ｌに対応するから、結局、血戦′
の容積？逐次検出し、その変化計（脈圧による）が最大
となるような平均カフ圧口？見い出せばこれが平均血圧
Ｐｂと一致することｖｃ７Ｚる。゛従って血管と無負荷
状態に保つため【ては、■ず容積変化が最大となる平均
カフ圧Ｐｃ（＝Ｐｂ）を検出し、次にこの平均カフ圧Ｆ
τに上述し７ｊ ｍＬ圧？打ち消すための変化分ΔＰｃ
を２１＜畳すればよい。By the way, it is known that the amplitude of the vibration of the blood vessel wall due to the pulse pressure O becomes maximum when the average cuff l (: J' c and the average blood pressure F1 match. 'i'fJ corresponds to the volume per unit length of the blood vessel (hereinafter simply referred to as the volume of Blood War II) and l to l, so in the end, Blood War'
The volume of? Average cuff pressure port that is detected sequentially and whose change meter (based on pulse pressure) is maximum? If found, it will be found that this matches the average blood pressure Pb. Therefore, in order to maintain the blood vessel in an unloaded state, first detect the average cuff pressure Pc (=Pb) at which the volume change is maximum, and then calculate the average cuff pressure F
7j mL pressure mentioned above for τ? Change amount ΔPc for canceling
All you have to do is fold 21<.
そしてこの無負荷状態においては血管壁ＣでＧコ何らの
力も作用しないから血管σ）容積は一定に保たれる０次に、血管の容積は血管？挾むように対間して配置され
た発光ダイオード（１，ＥＬ））とフォトトランジスタ
からなるツＣ学センサ（以ド、容積センサという）Ｖｒ
Ｃよって検出ぎｎる。すなわち、血管を流しる血液（赤
血球）に含ｆれるヘモグロビンは可視光領域に強い吸収
帯？持っているので、血管の容積が太さいけど前記フォ
トトランジスタに到達する透過元社が減少する。従って
血管に印加されるカフ圧Ｐｃが増加し血管の容積が減少
すると・透過ツＣ計が増しフォトトランジスタの出方型
１王（ｐ）下容積信号という）Ｓｖが高くなる０テた、
脈圧による容積変化が大さいほど容積信号Ｓ ｖの振幅
も大さくなり、血管の容積が一定ならば容積信号Ｓｖも
一定′と婦。こうして、血・管の容積は容積センサｔで
よって検出きれる。In this unloaded state, no force acts on the blood vessel wall C, so the volume of the blood vessel σ) remains constant.0 Next, what is the volume of the blood vessel? A volumetric sensor (hereinafter referred to as a volumetric sensor) Vr consisting of a light emitting diode (1, EL) and a phototransistor arranged in a pair in a sandwiching manner.
It is detected by C. In other words, does hemoglobin contained in blood (red blood cells) flowing through blood vessels have a strong absorption band in the visible light region? Because of this, although the volume of the blood vessel is large, the amount of transmission that reaches the phototransistor is reduced. Therefore, when the cuff pressure Pc applied to the blood vessel increases and the volume of the blood vessel decreases, the transmittance C meter increases and the phototransistor output type 1 (p) lower volume signal) Sv increases.
The larger the volume change due to pulse pressure, the larger the amplitude of the volume signal Sv, and if the volume of the blood vessel is constant, the volume signal Sv is also constant. In this way, the volume of the blood vessel/vessel can be detected by the volume sensor t.
上述したところ？要約すると、容積補償法においては・
容積センサから得られる容積信号５ｖＶｃ基づいて、容
積イＢ号Ｓｖの脈波成分（以下容積脈波信号という）Ｓ
ｇが最大となるような平均カフ圧■？設定し、次にぜ積
脈波イご号８ｇがゼロとなるように（すなわち血管の容
積が一定となるようＣで）変化分△Ｐｃ２平均カフ圧匹
に重畳すれば、このとさのカフ圧Ｐｃ（＝Ｐｃ＋ΔＰｃ
）が時々刻々変化する血圧と等しくなるということであ
る。As mentioned above? To summarize, in the volume compensation method,
Based on the volume signal 5vVc obtained from the volumetric sensor, the pulse wave component (hereinafter referred to as volume pulse wave signal) S of volume I B Sv
Average cuff pressure that maximizes g?■? Then, by superimposing the change ΔPc2 on the average cuff pressure so that the blood pulse wave Igo 8g becomes zero (in other words, at C so that the volume of the blood vessel is constant), the cuff of this tosa Pressure Pc (=Pc+ΔPc
) is equal to the ever-changing blood pressure.
以下−図面に基づいて本発明の実ｔｆｆＬ例？説明する
Ｏ第１図は本発明の一実施例の梅成？示すブロック図であ
り、この図ＶＣおいて１は円環状のカフである。このカ
フ圧は被測定部位（本実施例においては指）２ＶＣ外圧
？印加するものであり、その内壁３，３は弾性薄膜から
なり、指２の外ｊ剤に圧着芒れている。士にカフ１の内
ｇ１５にはチューブ４と介して水等の液体５が併給され
、この液体５がリニアポンプ６、刀！］振器７ｆＣよっ
て万目圧ぎｎる。こノ場合、リニアポンプ（ｓ′は上述
した平均カフ圧Ｐｃｔ形成し、加振器７は変化分ΔＰｃ
ｅ印加するものである。こうしてカフ圧内に形成され
たカフ圧ＰＣ（−ＰＣ＋Δｆ’ｃ）Ｇま指２内のぐ脈を
経皮的に加圧する。そしてこの方７−圧Ｐｃがチューブ
４に連通する圧力センサ８ＶＣよって検出己れ、電気信
号として出力される。Below - an actual tffL example of the invention based on the drawings? Explain. Figure 1 shows an embodiment of the present invention. FIG. 1 is a block diagram showing the present invention, and in this figure VC, reference numeral 1 represents an annular cuff. Is this cuff pressure 2VC external pressure of the part to be measured (in this example, the finger)? The inner walls 3, 3 are made of an elastic thin film and are pressed against the external agent of the finger 2. A liquid 5 such as water is simultaneously supplied to g15 of the cuff 1 through a tube 4, and this liquid 5 is supplied to the linear pump 6 and the sword! ] Use the vibrator 7fC to apply ten-man pressure. In this case, the linear pump (s') forms the above-mentioned average cuff pressure Pct, and the vibrator 7 generates the variation ΔPc.
e is applied. The cuff pressure PC (-PC+Δf'c) G thus formed within the cuff pressure is percutaneously pressurized within the forefoot 2. This 7-pressure Pc is detected by a pressure sensor 8VC communicating with the tube 4 and output as an electrical signal.
一万、指２とカフ１の内壁３との間には発光ダイオード
（ＬＥＤ）９ａとフォトトランジスタ（Ｐｈ）９ｂとか
らなる容積センサ９とが介挿されている。この場合、Ｌ
ＥＤ９ａとＰｈ９ｂとは指２に挾むように相対量してい
なければならない。A volume sensor 9 consisting of a light emitting diode (LED) 9a and a phototransistor (Ph) 9b is inserted between the finger 2 and the inner wall 3 of the cuff 1. In this case, L
ED9a and Ph9b must be in relative amounts so that they can be held between fingers 2.
そして、ＬＥＤ９ａから発光されたツＣは舟２？嬬過し
てＰｈ９ｂに受光され、その受元硅は血管の容積に対応
する０従ってＰｈ９ｂの出７Ｊ ’Ｑｔ圧すなわち容積
信号Ｓｖも血管の容積に対応する。And is the light emitted from LED 9a boat 2? By mistake, the light is received by Ph9b, and its receiving source corresponds to the volume of the blood vessel. Therefore, the output 7J'Qt pressure of Ph9b, that is, the volume signal Sv, also corresponds to the volume of the blood vessel.
次に１１は容積信号Ｓｖと増幅する直流増幅Ｗ・であり
、直流増幅器１１の出７Ｅ電圧の直流分はオフセット亀
ギｖｆによって自由に増減でさるようＶＣなっている。Next, 11 is a DC amplifier W. which amplifies the volume signal Sv, and the DC component of the output voltage 7E of the DC amplifier 11 is set to VC so that it can be freely increased or decreased by the offset tortoise Vf.
例えばオフセット−圧Ｖｆ＝００とさｔＣ前記直流分が
ｔｏＶであったとし、こり状態と保ったｆ〒オフセット
電圧Ｖｆのみ全７ｖに変化させたとすると前記直流分ｃ
′ｉ３ Ｖとなる。こうして、この直流増幅器１１は、
容積信号ＳＶ を単に増幅するだけでなく、その直流分
と除去χする作用もなす。この場合、オフセント重圧Ｖ
ｆは一後述する制御と３１６において形成され、１２ビ
ツトのＤ／Ａコンバータ１７？介してｇｌ：給され６０
次に、■２はゲイン調節器であり、増幅率？変えること
のでさる直流ゴ曽幅器からなる。すなわち、このゲイン
調節器１２はスイッチ素子と抵抗との直列接続回路と何
組か並列ＶＣ接鋭してりるフィードバック回・路を翁−
し、前記各スイッチ素子？制御信号ＣＩによってオン／
オフし、これによってフィードバック回路の抵抗直を変
化させてゲインの蘭節と行うものである。こうしてゲイ
ン調節器１２は、Ｍ］副信号Ｃ１の直に応じて直流増１
１荀器１１の出力信号の振１１’ｆｌ＋を増減し容積脈
波信号Ｓｇ？出力ｆる。この容積脈波信号ＳｇはＡ／Ｌ
）コンバータ１８・と位相補償器１小とＶＣ供給される
。■ず、Ａ／１〕フンバータ１８は容積脈波イー＝ｆ号
Ｓｇとデジタル（Ｆｔ 停に変（灸し、このデジタル信
号−全バス１５と介して１ｌｉｌＪ御部１６に供給する
ｇビットのコンバータである。−万、位相補償ｊ？Ｅ
ｌ ４・ｆ′ｉ谷積容積、・１を波イ；ｆ％Ｓｇの位相
とシフｈしてこの信号をゲイン調節器１８＋ｆＣ供給す
る。このゲインＷ節器１８はゲイン調節器１２と日様の
購或を有し°、制御信号Ｃ２の１直に応じて前記（＋４
号の振幅と増減して励ｕ２信号Ｓ ｅ ｆ 形成し、こ
れ？ドライバ１９とスイーンチ２０のａ丁が点に供給す
る。ここでスイッチ２０は励振信号Ｓｅと制佃１部１６
からｂ打点に供給されるリニアポンプ駆コ信号と？ＣＣ
点点介してドライバ２１に切替え供給するもので、制御
部１６から供給される制御信号Ｃ１ｖｃよって１２ＴＩ
替えが行われるαそして、ドライバ１９力４０ｋ 函、
７２、ドライバ２１がリニアポンプ６ｌ−ｉ１勅する〇次Ｋ・カフ圧Ｐｃは圧ブ］センサ８０でよって検出され
、圧力センサ８からはカフ圧Ｐｅｐで比例する信歓が出
力される。そしてこの１３号が増幅器２４によって増幅
され、カフ圧信号Ｓ ｒ） Ｍ Ｌ −（Ａ ／ Ｄコ
ンバータ２５ＩＪで供給される。この人／Ｄコンバータ
２５はカフ圧１３号８１）とデジタル信号Ｏ？：変換し
・これとバス１５２介して制御Ｆ５１５１ ｆＳに供１
恰するｇピッｉのコンバータである。支に、２７りまブ
ラウン管告示装置等からなる表示部であり、カフ圧信号
５ｐＴｈ血圧として吸水するととも（Ｃ％制御部１６か
ら供給すれる血圧スケールト表示する。For example, if offset-voltage Vf = 00 and tC, and the DC component is toV, and f is kept in a stiff state, and only the offset voltage Vf is changed to 7V in total, then the DC component c
'i3 V. In this way, this DC amplifier 11
It not only simply amplifies the volume signal SV, but also removes its DC component. In this case, the offcent pressure V
f is formed in a control section 316, which will be described later, and is connected to a 12-bit D/A converter 17? via gl: supplied 60
Next, ■2 is a gain adjuster, and is it an amplification factor? It consists of a DC gauge that can be changed. That is, this gain adjuster 12 has a feedback circuit/circuit in which several sets of parallel VC contacts are connected to a series connection circuit of a switch element and a resistor.
And each switch element mentioned above? Turned on/off by control signal CI
The switch is turned off, thereby changing the resistance value of the feedback circuit and adjusting the gain. In this way, the gain adjuster 12 increases the direct current by 1 in response to the sub-signal C1.
1 Increase or decrease the amplitude 11'fl+ of the output signal of the unit 11, and increase or decrease the volume pulse wave signal Sg? Output f. This volume pulse wave signal Sg is A/L
) Converter 18 and phase compensator 1 are supplied with VC. ■A/1] The Humbatater 18 converts the volume pulse wave E=f Sg into a digital signal (Ft), and supplies this digital signal to the 1lilJ control unit 16 via the entire bus 15 to the g-bit converter. −10,000, phase compensation j?E
The phase of the wave A;f%Sg is shifted from the phase of the wave A;f%Sg, and this signal is supplied to the gain adjuster 18+fC. This gain W adjuster 18 has a gain adjuster 12 and the same value as the gain adjuster 12, and adjusts the above (+4
The amplitude of the signal increases and decreases to form the excitation u2 signal S e f ? A driver 19 and a number of sweepers 20 supply the point. Here, the switch 20 is connected to the excitation signal Se and the control section 16.
What is the linear pump drive signal supplied from to point b? C.C.
12TI is switched and supplied to the driver 21 via a point and a control signal C1vc supplied from the control section 16.
The change is made α and the driver 19 force 40k box,
72, the 0th K cuff pressure Pc which the driver 21 controls the linear pump 6l-i1 is detected by the pressure sensor 80, and the pressure sensor 8 outputs a signal proportional to the cuff pressure Pep. Then, this signal No. 13 is amplified by the amplifier 24 and supplied by the A/D converter 25IJ. : Converted and provided to control F5151 fS via bus 152 1
It is a converter of g-pi. The main part is a display section consisting of a 27-rem cathode ray tube notification device, etc., which displays the cuff pressure signal 5pTh as blood pressure (blood pressure scaled) supplied from the C% control section 16.
ざて、上述した構成？有する本実施例において血圧の測
定を行う場合、第１図ＩＣ示すようにカフェＶｃ指２と
挿入する。そして第２ ｉｉ ｔｉｃ示す時刻ｔ。So, what about the above configuration? When measuring blood pressure in this embodiment, the cafe Vc finger 2 is inserted as shown in FIG. and time t indicated by the second ii tic.
にスタートボタンと押上げると、制御部１６がスインチ
２０？ｂ接点側に切替え、ドライバ２１に１１″信号と
供給する。これによってドライバｚ１がリニアポンプ６
？駆動し、カフ圧Ｐｃは第１１（イ）に示すように直線
的に増加する。これによって同図（ロ）に示す容積、信
１号８ｖも次第に上昇し、やがて）電圧Ｐｃが被検者の
平均血圧ｐｂに近づくと血管壁に脈圧による振動が現わ
れ、これが容積信号Ｓｖに脈波として生じる。同図（ハ
）Ｇオこの脈波信号（すな゛わち容積脈波信号）Ｓｇの
波脣を示すものである。次に、カフ圧Ｐｃがざらに上昇
し、カフ圧ＰＣが平均血圧ｐｂと一致すると、上述した
ように容積脈波信号Ｓｇが最大振幅となる（なお、カフ
圧Ｐｃは直線的に徐々に変化させているのでＰ Ｃ７Ｐ
ｃとなる）。ぞしてこのときの容積信号Ｓｖの（直ｆ
Ｓ ｖ ｓ とサーボ目標敏、カフ圧Ｐｃの［Ｐｃ
５２サーボ１初ｊｌＪｌ圧といい、これらは制御部１６
に記憶される。そしてリニアポンプ６がざらに゛・駆動
Ｅ’れ、カフ圧Ｐｃが増加するとカフ圧Ｐｃ〉血圧Ｐｂ
となり、これによって容積脈波１信号Ｓｇは次第に小ど
くなり、やがてほぼゼロにＩで減少する。そ、して制御
部Ｌ６はｐ）圧Ｐｃが予め設定された士限脇（例え゛ば
／ｇＯ□１（ｇ）になると、今度はドライバ２１に１０
″橢号と供給してリニアポンプ６を逆ｌＪ慇動し、これ
によってカフ圧ＰＣ’ｒ：Ｗ。When the start button is pressed up, the control unit 16 switches to the switch 20? Switch to the b contact side and supply a 11" signal to the driver 21. This causes the driver z1 to switch to the linear pump 6.
? The cuff pressure Pc increases linearly as shown in 11th (A). As a result, the volume signal 8v shown in FIG. It occurs as a pulse wave. FIG. 3(C) G shows the range of this pulse wave signal (ie, volume pulse wave signal) Sg. Next, when the cuff pressure Pc gradually increases and the cuff pressure PC matches the mean blood pressure pb, the volume pulse wave signal Sg reaches its maximum amplitude as described above (the cuff pressure Pc gradually changes linearly). Because I let you do it, P C7P
c). Therefore, the (direction f) of the volume signal Sv at this time is
S v s, servo target sensitivity, and cuff pressure Pc [Pc
52 servo 1 initial jlJl pressure, these are the control unit 16
is memorized. Then, when the linear pump 6 is roughly driven and the cuff pressure Pc increases, the cuff pressure Pc>blood pressure Pb
As a result, the volume pulse wave 1 signal Sg gradually becomes smaller and eventually decreases to almost zero at I. Then, when the pressure Pc reaches a preset limit (for example, /gO□1 (g)), the control unit L6 instructs the driver 21 to
The linear pump 6 is pumped in reverse lJ by supplying the same signal as "0", thereby increasing the cuff pressure PC'r:W.
標的に減少させゐ。そして第２図の時刻ｔ 、ＶＣカフ
圧ｆ’ｃがサーボ目標値１’ｃｓ に減少した時仄でス
イ７＋２０Ｔｈａ接点制に切替え、リニアポンプ６と停
止させる。こうし下、カフ圧Ｐｃがサーボ目標１直Ｐｃ
ｓにセラ）７れ、平均カフ圧Ｐｃ−平均血圧ＰｂとなＶ
容積脈波信号Ｓｇの振幅が第２図（ハ）に示すように最
大となる。なお、上記サーボ目標値Ｐｃｓ検出動作の間
、ゲイン調節器１２のゲインは一定に保たれている。：
ｆに、容積信号Ｓｇの直流分か増１０し、容積脈波信号
８ｇの振圃が予め設定された範囲を超えると制御部１６
がオフ セット電圧Ｖｆとコントロールして前記振幅？
前記範ＩＨＩｖｃ引さ芙すように作用する。ｆに、制御
部Ｉ６は上記時刻１． ｖｃゲイン調節器１２に制御信
号ＣＩと送り容積脈波信号Ｓｇめ振幅？予め設定ぎわ、
た端となるように増減する。こうして、個人差にょる振
幅の差が除失され、一定振幅の容積脈波信号Ｓｇが得ら
れる。Reduce it to the target. Then, at time t in FIG. 2, when the VC cuff pressure f'c has decreased to the servo target value 1'cs, the switch 7+20Tha contact system is switched and the linear pump 6 is stopped. Under this condition, cuff pressure Pc is the servo target 1 shift Pc
s)7, the average cuff pressure Pc - the average blood pressure Pb and V
The amplitude of the volume pulse wave signal Sg becomes maximum as shown in FIG. 2 (c). Note that the gain of the gain adjuster 12 is kept constant during the servo target value Pcs detection operation. :
f, the DC component of the volume signal Sg is increased by 10, and when the amplitude of the volume pulse wave signal 8g exceeds a preset range, the controller 16
is controlled by the offset voltage Vf and the amplitude ?
It acts to subtract the range IHIvc. At time 1.f, the control unit I6 controls the time 1.f. The control signal CI and the amplitude of the sent volume pulse wave signal Sg are sent to the vc gain adjuster 12. Pre-set time,
It increases or decreases so that it reaches the end. In this way, differences in amplitude due to individual differences are eliminated, and a volume pulse wave signal Sg of constant amplitude is obtained.
以上の設定が終了すると、制御部１６は前記容積脈波信
号Ｓｇに基づいて加振器Ｌ７’ｔ−励振し、カフ圧ＰＣ
の変化分ΔＰ、ｃｌコントロールシ、容積脈波信号Ｓｙ
がゼロになるように、すなわち血管の容積が一定になる
よう、にフィードバック制御する０ざらに詳述すると、
制御部１６は第２図に示す時刻ｔ：にゲイン調節器１８
に制御信号Ｃ７？供給し、これによって励、振信号Ｓｅ
の振幅２４１２節しながら容積脈波１信号Ｓｇが次第に
小さくなるように、ドライバ１９？介ｔて万ロ振器７？
７．イードバック制御する。この場合、ｇ接脂波信号８
ｇは位相補償器１４によって位相がシフトされ、これに
よって７］ｌ］振器７Ｖｃよって形成ざ丘るカフ圧の変
化分へＰ Ｃと脈圧とが互に打消し合うようにコントロ
ールされる。こうして、第２図に示す時刻ｔ３に容積脈
波信号８ｇがほぼゼロになると、この時のカフ圧Ｐｃが
血圧Ｐｂと等しくなる。そしてカフ圧ＰＣはカフ圧信号
８ｐとして得られ、この信号Ｓｐが表示＠２７に血圧ス
ケールとともにリアルタイムで表示される。こうして表
示部２７には時々刻々変化する血圧の変動状態が表示さ
れる。なお、時刻ｔ２以後、オフセント電圧Ｖｆとゲイ
ン調節器１２のゲインは共に一定に維Ｎぎれる。。そ、
して、時刻ｔ２以後に平均血圧Ｐｂが変化己これによっ
て容積脈波信号ＳｇＶＣ直流分が重畳された場合は、こ
の直流分が位相補償器１屯。When the above settings are completed, the control unit 16 excites the vibrator L7't- based on the volume pulse wave signal Sg, and controls the cuff pressure PC.
change ΔP, cl control signal, volume pulse wave signal Sy
Feedback control is performed so that the volume of the blood vessel becomes zero, that is, the volume of the blood vessel is constant.
The control unit 16 controls the gain adjuster 18 at time t shown in FIG.
control signal C7? and thereby the excitation and oscillation signal Se
The driver 19? Intermediate million roller shaker 7?
7. Control feedback. In this case, g greasy wave signal 8
The phase of g is shifted by the phase compensator 14, thereby controlling the change in cuff pressure generated by the vibrator 7Vc so that Pc and pulse pressure cancel each other out. In this way, when the volume pulse wave signal 8g becomes almost zero at time t3 shown in FIG. 2, the cuff pressure Pc at this time becomes equal to the blood pressure Pb. Then, the cuff pressure PC is obtained as a cuff pressure signal 8p, and this signal Sp is displayed on the display @27 in real time together with the blood pressure scale. In this way, the display unit 27 displays the fluctuation state of blood pressure that changes from moment to moment. Note that after time t2, both the offset voltage Vf and the gain of the gain adjuster 12 remain constant. . So,
Then, when the mean blood pressure Pb changes after time t2, and as a result, the DC component of the volume pulse wave signal SgVC is superimposed, this DC component is used as the phase compensator.
ゲイン調節器１８２介ｔでドライバ２１に供給されリニ
アポンプ６が駆動キ２する。そして再び平均カフ圧Ｐｃ
が平均血圧Ｐｂと等しくなるようにフィードバック制御
される。The signal is supplied to the driver 21 through the gain adjuster 182, and the linear pump 6 is driven. And again the average cuff pressure Pc
is feedback-controlled so that it becomes equal to the average blood pressure Pb.
なお、上記表示部２？に：は他の情報・例えば心電図？
血圧と同時Ｖｃｉ示すすることも可能である。In addition, the above-mentioned display part 2? N: Is there other information, such as an electrocardiogram?
It is also possible to display Vci at the same time as blood pressure.
以上説明したようにこの発明に、容積補償法によ、る血
圧測定と全自動的に行えるようにしたので、ｍｌ続的な
血圧測定？極めて容易に行うことのでさる利点が得られ
る。As explained above, in this invention, blood pressure measurement can be performed fully automatically using the volume compensation method, so it is possible to measure blood pressure continuously. A great advantage is that it is extremely easy to perform.
第１口は本発明の一実施例の構成？示すプロツり図、第
１図は同実施例便用時の各部波形と示す波形図であり、
同図（イ）Ｇまクツ圧Ｐｃの波形図、（ロ）は容積信号
８ ｖの波形図、同図（／→は容積脈波信号Ｓｇの波形
図である。１・・・・・・カフ、７・・・・・・刀口振器、８・・
パ・・圧力セン→１．９・・・・・・容積センサ。出即人 株式会社 ウ゛工□ダ鰻作所Is the first port an embodiment of the present invention? The plot diagram shown in FIG. 1 is a waveform diagram showing the waveforms of various parts when using the same example,
In the same figure, (A) is a waveform diagram of the G eyelid pressure Pc, (B) is a waveform diagram of the volume signal 8V, and in the same figure (/→ is a waveform diagram of the volume pulse wave signal Sg. 1... Cuff, 7... Blade shaker, 8...
Pa... Pressure sensor → 1.9... Volume sensor. Derived from Wiko Co., Ltd. Da Unagi Farm
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP58030500AJPS59156325A (en) | 1983-02-25 | 1983-02-25 | Indirect blood pressure measuring apparatus |
| US06/491,984US4524777A (en) | 1983-02-25 | 1983-05-05 | Automatic, continuous and indirect blood pressure measurement apparatus |
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP58030500AJPS59156325A (en) | 1983-02-25 | 1983-02-25 | Indirect blood pressure measuring apparatus |
| Publication Number | Publication Date |
|---|---|
| JPS59156325Atrue JPS59156325A (en) | 1984-09-05 |
| JPH0131370B2 JPH0131370B2 (en) | 1989-06-26 |
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP58030500AGrantedJPS59156325A (en) | 1983-02-25 | 1983-02-25 | Indirect blood pressure measuring apparatus |
| Country | Link |
|---|---|
| US (1) | US4524777A (en) |
| JP (1) | JPS59156325A (en) |
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